WO1991010474A1 - Ensemble fibroptique de lentille submersible - Google Patents
Ensemble fibroptique de lentille submersible Download PDFInfo
- Publication number
- WO1991010474A1 WO1991010474A1 PCT/US1990/006472 US9006472W WO9110474A1 WO 1991010474 A1 WO1991010474 A1 WO 1991010474A1 US 9006472 W US9006472 W US 9006472W WO 9110474 A1 WO9110474 A1 WO 9110474A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- lens
- submersible
- optical fiber
- fiber
- fiberoptic assembly
- Prior art date
Links
- 239000000835 fiber Substances 0.000 claims abstract description 53
- MCMNRKCIXSYSNV-UHFFFAOYSA-N Zirconium dioxide Chemical compound O=[Zr]=O MCMNRKCIXSYSNV-UHFFFAOYSA-N 0.000 claims abstract description 40
- 239000013307 optical fiber Substances 0.000 claims abstract description 37
- 238000011282 treatment Methods 0.000 claims abstract description 14
- 239000011248 coating agent Substances 0.000 claims description 3
- 238000000576 coating method Methods 0.000 claims description 3
- 229910001369 Brass Inorganic materials 0.000 claims description 2
- 239000010951 brass Substances 0.000 claims description 2
- 238000004519 manufacturing process Methods 0.000 abstract description 3
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 12
- 230000003287 optical effect Effects 0.000 description 11
- 238000002428 photodynamic therapy Methods 0.000 description 7
- 239000000463 material Substances 0.000 description 6
- 238000010276 construction Methods 0.000 description 5
- 229910052751 metal Inorganic materials 0.000 description 5
- 239000002184 metal Substances 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 239000004593 Epoxy Substances 0.000 description 3
- 239000008280 blood Substances 0.000 description 3
- 210000004369 blood Anatomy 0.000 description 3
- 238000009826 distribution Methods 0.000 description 3
- XKRFYHLGVUSROY-UHFFFAOYSA-N Argon Chemical compound [Ar] XKRFYHLGVUSROY-UHFFFAOYSA-N 0.000 description 2
- RTZKZFJDLAIYFH-UHFFFAOYSA-N Diethyl ether Chemical compound CCOCC RTZKZFJDLAIYFH-UHFFFAOYSA-N 0.000 description 2
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 239000002245 particle Substances 0.000 description 2
- 230000005855 radiation Effects 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- QCWXUUIWCKQGHC-UHFFFAOYSA-N Zirconium Chemical compound [Zr] QCWXUUIWCKQGHC-UHFFFAOYSA-N 0.000 description 1
- 229910052786 argon Inorganic materials 0.000 description 1
- 238000000429 assembly Methods 0.000 description 1
- 230000000712 assembly Effects 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 238000009835 boiling Methods 0.000 description 1
- 238000005266 casting Methods 0.000 description 1
- 238000005253 cladding Methods 0.000 description 1
- 238000004140 cleaning Methods 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 230000004907 flux Effects 0.000 description 1
- 230000014509 gene expression Effects 0.000 description 1
- CPBQJMYROZQQJC-UHFFFAOYSA-N helium neon Chemical compound [He].[Ne] CPBQJMYROZQQJC-UHFFFAOYSA-N 0.000 description 1
- 238000005286 illumination Methods 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 230000004807 localization Effects 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 230000000704 physical effect Effects 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
- 238000007789 sealing Methods 0.000 description 1
- 230000035939 shock Effects 0.000 description 1
- 229920002379 silicone rubber Polymers 0.000 description 1
- 239000000779 smoke Substances 0.000 description 1
- 238000004018 waxing Methods 0.000 description 1
- 229910052726 zirconium Inorganic materials 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N5/0601—Apparatus for use inside the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N5/0613—Apparatus adapted for a specific treatment
- A61N5/062—Photodynamic therapy, i.e. excitation of an agent
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
- G02B23/16—Housings; Caps; Mountings; Supports, e.g. with counterweight
- G02B23/22—Underwater equipment
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
- G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
- G02B23/2407—Optical details
- G02B23/2423—Optical details of the distal end
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
- G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
- G02B23/26—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes using light guides
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/24—Coupling light guides
- G02B6/26—Optical coupling means
- G02B6/32—Optical coupling means having lens focusing means positioned between opposed fibre ends
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/24—Coupling light guides
- G02B6/42—Coupling light guides with opto-electronic elements
- G02B6/4201—Packages, e.g. shape, construction, internal or external details
- G02B6/4202—Packages, e.g. shape, construction, internal or external details for coupling an active element with fibres without intermediate optical elements, e.g. fibres with plane ends, fibres with shaped ends, bundles
- G02B6/4203—Optical features
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
- A61B2018/2255—Optical elements at the distal end of probe tips
- A61B2018/2261—Optical elements at the distal end of probe tips with scattering, diffusion or dispersion of light
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/24—Coupling light guides
- G02B6/26—Optical coupling means
- G02B6/32—Optical coupling means having lens focusing means positioned between opposed fibre ends
- G02B6/325—Optical coupling means having lens focusing means positioned between opposed fibre ends comprising a transparent member, e.g. window, protective plate
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/24—Coupling light guides
- G02B6/36—Mechanical coupling means
- G02B6/3628—Mechanical coupling means for mounting fibres to supporting carriers
- G02B6/3632—Mechanical coupling means for mounting fibres to supporting carriers characterised by the cross-sectional shape of the mechanical coupling means
- G02B6/3644—Mechanical coupling means for mounting fibres to supporting carriers characterised by the cross-sectional shape of the mechanical coupling means the coupling means being through-holes or wall apertures
Definitions
- the present invention relates to a submersible lens fiberoptic assembly for use in a biological ' environment, and especially to a submersible ball lens fiberoptic assembly for photodynamic therapy treatments (hereinafter referred to as PDT) for transferring radiation from an optical fiber to surrounding tissue.
- PDT photodynamic therapy treatments
- Figure 1A shows an arrangement known as a cylindrical diffuser.
- a cylindrical optical element 11 is butted against an optical fiber 12, and functions to cylindrically diffuse light coupled into it via the optical fiber.
- Figure IB shows a prior an arrangement known as a spherical diffuser.
- a spherical optical element In this, a spherical optical element
- FIG. 3C A third prior art arrangement is shown in Figure 3C, this being an arrangement known as a submersible microlens.
- a housing 16 encloses a miniature lens
- the end of an optical fiber 19 is positioned at the back focal point of the lens 17.
- the location of the back focal point of the lens is influenced by the index of refraction of the lens and of the medium in contact with the lens and • the optical fiber surface.
- the back focal point is fixed by sealing the fiber and lens in air through use of the housing 16 and window or cover plate 18.
- the ideal assembly for coupling radiation from an optical fiber into tissue is one which produces a highly divergen beam of light whose cross section everywhere, in air or water, is a magnified image of the optical fiber end or face. While the arrangement of Figure 1C does achieve many of these objectives, the construction is complicated and accordingly expensive to manufacture.
- a submersible lens fiberoptic assembly for use in a biological environment, especially in PDT treatments, has an optical fiber with an end for emitting light energy, a fiber jacket for fixing and protecting the optical fiber, a lens made of zirconia for transferring the light beam and controlling the beam divergence, and a housing for fixing the fiber jacket and the lens.
- zirconia has good properties of resisting mechanical and thermal shock, there is no need to use a window as in the case of the prior art.
- the lens is a ball lens
- the fiber jacket and housing is in a threaded connection so that the distance between the optical fiber face and the ball lens, can be adjusted by simply rotating the housing on the jacket.
- the assembly Since the lens is a ball shape, the assembly has good divergent and image formation properties.
- the present invention provides a novel submersible lens fiberoptic assembly for use in PDT treatments using a hemisphere lens with its spherical surface facing the optical fiber end for transferring the light beam to areas which are inaccessible to a normal "forward looking" lens.
- FIGS 1A, IB and 1C show three different types of prior art assemblies used for light delivery in PDT treatments.
- Figure 2 shows a preferred embodiment of the submersible ball lens fiberoptic assembly of the present invention.
- Figure 3 is a schematic ray diagram of a 1mm zirconia ball lens in air of the submersible ball lens fiberoptic assembly of the present invention.
- Figure 4. ⁇ shows schematically the ray trace of the output beam of a 1mm zirconia ball lens in air.
- Figure 5 is a diagram of the light distribution across a spot at 4.1 cm from a 1mm diameter zirconia ball lens of the submersible ball lens fiberoptic assembly of the present invention.
- Figure 6 is a schematic ray diagram of an 0.8mm diameter zirconia ball lens in air of present invention.
- Figure 7 is a schematic ray diagram of an 0.6mm diameter zirconia ball lens in air of the present invention.
- Figure 8a shows schematically the changes of light beam diameter with respect to distance from the lens for lmm, 0.8mm and 0.6mm zirconia ball lenses in water and in air of the present submersible ball lens fiberoptic assembly.
- Figure 8b shows schematically the changes of- light beam diameter with respect to distance from lens for lmm, 0.8mm and 0.6mm zirconia ball lenses in air of the present submersible ball lens fiberoptic assembly.
- Figures 9A, 9B and 9C show schematically three different arrangements of another preferred embodiment of the present invention which can deliver the light beam to the treatment areas inaccessible to a "forward looking" lens.
- Figure 10 shows schematically an embodiment of the housing having a top cover portion used in a side looking submersible lens fiberoptic assembly of the present invention.
- a preferred embodiment of the submersible lens fiberoptic assembly of the present invention includes a ball lens 20, an optical fiber 21 having a fiber jacket 22 and a cylindrical housing 23.
- the ball lens 20 is preferably made of zirconia because of its mechanical, thermal and optical properties. Specifically, zirconia is a very hard material. If a zirconia ball is placed on a lab table and struck with a carpenter's hammer, for example, the table top acquires a dent, but there is no visible damage to the ball. . This ability to withstand rough handling simplifies the assembly procedure.
- the cylindrical housing 23 can be made of metal, such as brass. One end of the metal housing is drilled to take the press-fitted ball lens 20.
- the metal housing 23 and the fiber jacket 22 are preferably threadedly coupled so that the distance between the optical fiber face and the ball lens can be adjusted precisely by simply rotating the housing 23.
- the pressfit and the tight thread on the fiber jacket make a water tight seal to the air chamber (generally indicated by reference numeral 24) on the input side of the ball. Care must be taken to insure that this, volume is free of particles during assembly since the ball lens produces an enlarged image of particles lying on the face of the fiber.
- the exposed surface of the ball lens 20 needs no special protection or cleaning procedure. This was demonstrated in an experiment wherein a ball lens fiberoptic was coupled to an argon pumped dye laser and submerged in a test tube of human blood. The dye laser power was increased until the blood adjacent to the lens surface was boiling vigorously. The ball lens fiberoptic was withdrawn and allowed to "smoke.” The baked blood was scraped from the lens surface with a knife edge and the surface was wiped clean with an alcohol soaked gauze. The focused spot using this ball lens appeared to be the same as before the test.
- the ball lens 20 is a lmm diameter precision optical sphere made of zirconia, and the metal housing or cylinder 23 is drilled through from the opposite end- to take a 120 thread per inch tap. Suitable zirconium spheres are commercially available from Precomp Inc., of Great Neck, New York.
- the metal housing is threaded into the jacket 22 of a 400 micrometer diameter optical fiber until the polished fiber end is in contact with the sphere, and then backed off one-half turn.
- the back focal point for the submerged ball lens assembly is 108 micrometers from the surface of the ball lens. This is a half turn of the thread.
- the back focal point- for the lens in air is inaccessible, being 33 micrometers inside the ball. However, the fiber end is nearly focused in air and appears sharp in water, even if the fiber is in contact with the ball.
- the ray traces are symmetrical about the optical axis (the line through the center of the sphere and perpendicular to the fiber face). All rays from the fiber having a common direction are focused by the input surface at a point inside the ball. Three such focal points are shown in Figure 3 for the three rays of the cone. This focusing of the rays inside the lens occurs because the lens is spherical, its index of refraction is ' greater than 2, and the input surface of the sphere is in air. The light beam has its smallest diameter inside the sphere. The rays diverge from the focal points and are refracted at the output surface to form a more (in air) or less (in water) rapidly diverging beam.
- the rays of the output beam near the lens in Figure 3 are extended in Figure 4 into the far field.
- the points of origin of the rays are indicated by the numbers on the right of the drawing.
- the rays from any point on the fiber face appear in the output beam as nearly parallel rays and are on the opposite side of the optical axis.
- the three diverging rays from the top of the fiber in Figure 3 appear in Figure 4 as three nearly parallel rays at the bottom of the beam.
- any cross section of the beam in the far field of the lens is a magnified, inverted, nearly focused image of the fiber face. Therefore, there is no need for a window on the lens as is the case with the prior art.
- Approximate but useful expressions can be derived from paraxial ray equations for the output beam divergence and the beam diameter at the output surface of the ball lens. These equations show how physical properties of the fiber, ball lens and medium in which the ball lens is submerged determine output beam parameters.
- the equations are:
- N.A. the numerical aperture of the. fiber in air
- equation (2) A practical application of equation (2) is the calculation of the beam intensity (watts/cm 2 ) at the exposed surface of the ball lens.
- the beam diameter at the ball surface is 0.23 mm.
- Eighty milliwatts are required to treat a 1 cm diameter tumor at a power density of 100 mW/cm 2 .
- the beam intensity at the ball surface calculates to be 190 watts/cm 2 , a substantial energy flux.
- the beam intensity drops to 100 mW/cm 2 at 11 mm from the lens in air.
- Figure 5 is a plot of the measured light distribution across a spot at 4.1 cm from a 1 mm ball lens.
- the ball lens fiber was coupled to a helium-neon laser (633 nm wavelength) whose output was chopped at 1.5 kHz.
- the instrumentation consisted of a model 4010 Laserguide fiberoptic light guide, a photodetector, an amplifier phase locked to the 1.5 kHz signal, and a digital voltmeter.
- the light guide is a spherical diffuser normally used in PDT treatments of the bladder. It produces •" a spherically symmetric light field from a 1.7 mm diameter sphere of light diffusing material. Used in reverse it collects light from almost all directions.
- the illumination is 80% or better of the maximum value. ⁇ over most of the beam cross section. The distribution is not exactly symmetrical because the ball and fiber were not perfectly aligned. The peaks near the center and the edge may be due to multiple reflections.
- Smaller diameter balls produce beams of greater divergence as shown in Figures 6 and 7, relating respectively to 0.8 mm and 0.6 mm ball lens.
- the interior focal points- are not as well defined in the 0.6 mm ball lens as in the 1 mm ball lens. This may indicate a fall-off in image quality with increasing curvature of the refractory surface.
- the trace of the horizontal ray emitted from the edge of the fiber is used to define the output beam size.
- the angle which this ray makes with the optical axis after refraction at the output surface is the half-angle beam divergence. This ray appears to come from a point on the optical axis close to the output surface of the sphere. Therefore, the beam diameter at any distance from the lens is given by twice the product of this distance and the tangent of the half angle divergence.
- Beam diameter plots for lmm, 0.8 mm and 0.6 mm ball lenses in water and in air are shown in Figures 8A and 8B, respectively.
- the full angle of the beam divergence is given next to each curve. These angles are smaller when the ball lens is submerged because water reduces the refraction of rays at the output surface.
- the measured values for the 1 mm ball lens are in agreement with the theoretical prediction.
- the Laserguide Microlens Model 5060 has the same divergence as that predicted for an 800 micron diameter ball lens.
- FIGS 9A, 9B and 9C there is shown another preferred embodiment of the submersible lens fiberoptic system of the present invention which can be used in conjunction with side looking fiberoptic scopes for treatment of areas inaccessible to a "forwarding looking" lens.
- the lens is a hemisphere lens made of zirconia and its spherical surface faces the optical • fiber end.
- This type of submersible lens fiberoptic system can produce an output beam at angles up to 120° from the fiber axis. If air is maintained at the plane surface, total internal reflection (TIR) would occur for beam deflection up to 90°. At larger angles a reflective coating would be required.
- FIG 9.A, 9B and 9C show the different arrangements under which the output beams of the system are at angles 60°, 90° and 120° from the fiber axis, respectively.
- Figure 10 shows an embodiment of the housing 30 used to fix the fiber jacket 22 and lens 20 of the side looking submersible lens fiberoptic assembly.
- the housing 30, besides the sleeve configuration 23 discussed in the forward looking assembly, further includes a top cover portion 25 which " has a circular opening 27 on its side functioning as a light output passage, and an air cap 26 fitted on the hemisphere lens 20 to provide an air chamber
- the top cover portion is preferably made of plastic material such as epoxy.
- the top cover portion can be formed in the following way.
- the fiber system and lens with an air cap are first held by an appropriate device and correct alignment of the sphere to the fiber is made.
- the lens is fixed to the fiber system by a waxing fixture and put into a silicon rubber mold for casting epoxy.
- the fiber jacket 22 is unscrewed from the assembly and the wax is removed with ether or hot water to provide a air chamber 24 between the lens and fiber.
- the fiber is cleaned and threaded back to a proper focus for use.
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- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biomedical Technology (AREA)
- Engineering & Computer Science (AREA)
- Optics & Photonics (AREA)
- General Physics & Mathematics (AREA)
- Pathology (AREA)
- Public Health (AREA)
- Astronomy & Astrophysics (AREA)
- Veterinary Medicine (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Biophysics (AREA)
- Surgery (AREA)
- Molecular Biology (AREA)
- Medical Informatics (AREA)
- Heart & Thoracic Surgery (AREA)
- Optical Couplings Of Light Guides (AREA)
- Radiation-Therapy Devices (AREA)
- Optical Fibers, Optical Fiber Cores, And Optical Fiber Bundles (AREA)
Abstract
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP3501052A JPH10511005A (ja) | 1990-01-08 | 1990-11-05 | 可潜レンズファイバオプチック組立体 |
CA002075489A CA2075489C (fr) | 1990-01-08 | 1990-11-05 | Assemblage de fibre optique pour lentilles submersibles |
DE69026960T DE69026960T2 (de) | 1990-01-08 | 1990-11-05 | Tauchanordnung mit linse und optischer faser |
EP91900535A EP0510007B1 (fr) | 1990-01-08 | 1990-11-05 | Ensemble fibroptique de lentille submersible |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US46163690A | 1990-01-08 | 1990-01-08 | |
US461,636 | 1990-01-08 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1991010474A1 true WO1991010474A1 (fr) | 1991-07-25 |
Family
ID=23833355
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1990/006472 WO1991010474A1 (fr) | 1990-01-08 | 1990-11-05 | Ensemble fibroptique de lentille submersible |
Country Status (7)
Country | Link |
---|---|
US (2) | US5190536A (fr) |
EP (2) | EP0682956B1 (fr) |
JP (1) | JPH10511005A (fr) |
AU (1) | AU6897991A (fr) |
CA (1) | CA2075489C (fr) |
DE (2) | DE69026960T2 (fr) |
WO (1) | WO1991010474A1 (fr) |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2001042770A1 (fr) * | 1999-12-11 | 2001-06-14 | Qualico Gmbh | Dispositif de detection des caracteristiques d'une bande papier defilante |
US6624187B1 (en) | 2000-06-12 | 2003-09-23 | Health Research, Inc. | Long wave length absorbing bacteriochlorin alkyl ether analogs |
EP2105779A3 (fr) * | 2008-03-21 | 2009-11-18 | FUJIFILM Corporation | Système optique d'éclairage pour endoscope et procédé d'assemblage associé |
US7820143B2 (en) | 2002-06-27 | 2010-10-26 | Health Research, Inc. | Water soluble tetrapyrollic photosensitizers for photodynamic therapy |
US7897140B2 (en) | 1999-12-23 | 2011-03-01 | Health Research, Inc. | Multi DTPA conjugated tetrapyrollic compounds for phototherapeutic contrast agents |
EP2329759A1 (fr) * | 2004-09-29 | 2011-06-08 | The General Hospital Corporation | Système et procédé d'imagerie à cohérence optique |
Families Citing this family (58)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1991010474A1 (fr) * | 1990-01-08 | 1991-07-25 | Health Research, Incorporated | Ensemble fibroptique de lentille submersible |
US5370649A (en) * | 1991-08-16 | 1994-12-06 | Myriadlase, Inc. | Laterally reflecting tip for laser transmitting fiber |
US5361316A (en) * | 1992-03-05 | 1994-11-01 | Lederle (Japan) Ltd. | Optical fiber laser device for transmitting a pulse laser beam |
US5363461A (en) * | 1993-07-20 | 1994-11-08 | Bergmann Ernest E | Field installable optical fiber connectors |
DE69514262T2 (de) * | 1994-03-23 | 2001-10-11 | Yasuo Hashimoto | Katheter mit Lichtleitfaser |
US5496309A (en) * | 1994-05-06 | 1996-03-05 | Trimedyne, Inc. | Catheter device utilizing a laser beam laterally directed by a high index prism in a liquid medium |
DE9409616U1 (de) * | 1994-06-17 | 1994-08-04 | Fa. Carl Zeiss, 89520 Heidenheim | Applikator zur Behandlung eines erhöhten Augeninnendruckes mittels Laserstrahlung |
US6123715A (en) | 1994-07-08 | 2000-09-26 | Amplatz; Curtis | Method of forming medical devices; intravascular occlusion devices |
US5591161A (en) * | 1995-10-25 | 1997-01-07 | Plc Medical Systems, Inc. | Angled beam delivery handpiece for laser or other monochromatic light source |
US5836939A (en) * | 1995-10-25 | 1998-11-17 | Plc Medical Systems, Inc. | Surgical laser handpiece |
US5833683A (en) * | 1996-01-12 | 1998-11-10 | Surgical Laser Technologies, Inc. | Laterally-emitting laser medical device |
US5784508A (en) * | 1996-02-09 | 1998-07-21 | Turner; R. Scott | Ball, wide-angle illuminator for eye surgery |
US5782825A (en) * | 1996-03-07 | 1998-07-21 | Miravant Systems, Inc. | Microlens tip assembly for light delivery catheter |
US5807383A (en) * | 1996-05-13 | 1998-09-15 | United States Surgical Corporation | Lasing device |
US6283955B1 (en) | 1996-05-13 | 2001-09-04 | Edwards Lifesciences Corp. | Laser ablation device |
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- 1990-11-05 EP EP95108356A patent/EP0682956B1/fr not_active Expired - Lifetime
- 1990-11-05 EP EP91900535A patent/EP0510007B1/fr not_active Expired - Lifetime
- 1990-11-05 DE DE69026960T patent/DE69026960T2/de not_active Expired - Fee Related
- 1990-11-05 JP JP3501052A patent/JPH10511005A/ja active Pending
- 1990-11-05 AU AU68979/91A patent/AU6897991A/en not_active Abandoned
- 1990-11-05 DE DE69033449T patent/DE69033449T2/de not_active Expired - Fee Related
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WO2001042770A1 (fr) * | 1999-12-11 | 2001-06-14 | Qualico Gmbh | Dispositif de detection des caracteristiques d'une bande papier defilante |
US6586739B2 (en) | 1999-12-11 | 2003-07-01 | Metso Automation Oy | Device for detecting characteristics of a moving paper web |
US7897140B2 (en) | 1999-12-23 | 2011-03-01 | Health Research, Inc. | Multi DTPA conjugated tetrapyrollic compounds for phototherapeutic contrast agents |
US6624187B1 (en) | 2000-06-12 | 2003-09-23 | Health Research, Inc. | Long wave length absorbing bacteriochlorin alkyl ether analogs |
US7820143B2 (en) | 2002-06-27 | 2010-10-26 | Health Research, Inc. | Water soluble tetrapyrollic photosensitizers for photodynamic therapy |
USRE43274E1 (en) | 2002-06-27 | 2012-03-27 | Health Research, Inc. | Fluorinated photosensitizers related to chlorins and bacteriochlorins for photodynamic therapy |
EP2329759A1 (fr) * | 2004-09-29 | 2011-06-08 | The General Hospital Corporation | Système et procédé d'imagerie à cohérence optique |
USRE43875E1 (en) | 2004-09-29 | 2012-12-25 | The General Hospital Corporation | System and method for optical coherence imaging |
USRE45512E1 (en) | 2004-09-29 | 2015-05-12 | The General Hospital Corporation | System and method for optical coherence imaging |
EP2105779A3 (fr) * | 2008-03-21 | 2009-11-18 | FUJIFILM Corporation | Système optique d'éclairage pour endoscope et procédé d'assemblage associé |
Also Published As
Publication number | Publication date |
---|---|
CA2075489A1 (fr) | 1991-07-09 |
JPH10511005A (ja) | 1998-10-27 |
DE69033449D1 (de) | 2000-03-09 |
US5403308A (en) | 1995-04-04 |
EP0510007B1 (fr) | 1996-05-08 |
EP0682956B1 (fr) | 2000-02-02 |
DE69026960D1 (de) | 1996-06-13 |
EP0682956A2 (fr) | 1995-11-22 |
DE69026960T2 (de) | 1996-09-05 |
DE69033449T2 (de) | 2000-10-12 |
AU6897991A (en) | 1991-08-05 |
CA2075489C (fr) | 2002-01-01 |
EP0510007A1 (fr) | 1992-10-28 |
EP0682956A3 (fr) | 1996-07-17 |
EP0510007A4 (en) | 1993-03-31 |
US5190536A (en) | 1993-03-02 |
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